JP2018191848A - X-ray diagnostic apparatus and medical image diagnostic system - Google Patents

Abstract

To generate a superimposition image with time sequences matched in superimposing images acquired in real time from different modalities.SOLUTION: An X-ray diagnostic apparatus includes a start trigger acquisition part, a frame rate setting part, a first acquisition part, a second acquisition part, and a superimposition image generation part. The start trigger acquisition part acquires a start trigger on the basis of biological information on a subject from the other modality. The frame rate setting part sets a second frame rate based on a first frame rate on the acquisition of a medical image by the other modality. The first acquisition part acquires an X-ray image at the second frame rate in real time, triggered by the start trigger. The second acquisition part acquires a medical image in real time, in parallel with the acquisition of the X-ray image. The superimposition image generation part generates superimposition images that superimpose the X-ray image on the medical image sequentially.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to an X-ray diagnostic apparatus and a medical image diagnostic system.

  Currently, an X-ray diagnostic apparatus has a function of displaying, for example, an X-ray image and an ultrasonic image (or an X-ray moving image and an ultrasonic moving image) superimposed on each other. This type of X-ray diagnostic apparatus may superimpose, for example, an X-ray image acquired in advance and an ultrasonic image acquired in advance from another modality (medical image diagnostic apparatus) by the above function. The X-ray diagnostic apparatus may superimpose an ultrasonic image acquired in advance from another modality on an X-ray fluoroscopic image acquired in real time, for example, by the above function.

JP 2014-61093 A

  However, the X-ray diagnostic apparatus as described above is not particularly problematic in the case described above, but according to the study of the present inventor, in the case of superimposing X-ray images and ultrasonic images acquired in real time, respectively. There is a possibility that a time-series shifted superimposed image is generated. For example, there is a possibility that the timing for starting the acquisition of the X-ray image and the timing for starting the acquisition of the ultrasonic image do not coincide with each other due to the difference between the clock of the X-ray diagnostic apparatus and the clock of the ultrasonic diagnostic apparatus. In addition, there is a possibility that the image update rate is shifted in the superimposed image of the X-ray image and the ultrasonic image.

  An object of the present invention is to provide an X-ray diagnostic apparatus and a medical image diagnostic system that can generate a superimposed image having a uniform time series when images acquired in real time from different modalities are superimposed.

  According to the embodiment, the X-ray diagnostic apparatus includes a start trigger acquisition unit, a frame rate setting unit, a first acquisition unit, a second acquisition unit, and a superimposed image generation unit. The start trigger acquisition unit acquires a start trigger indicating the start of X-ray image acquisition based on the biological information of the subject from another modality. The frame rate setting unit sets a second frame rate related to acquisition of an X-ray image based on a first frame rate related to acquisition of a medical image by another modality. The first acquisition unit acquires an X-ray image of the subject in real time at the second frame rate, triggered by the start trigger. The second acquisition unit acquires the medical image of the subject from other modalities in real time in parallel with the acquisition of the X-ray image. The superimposed image generation unit sequentially generates a superimposed image obtained by superimposing the acquired X-ray image and the acquired medical image.

It is a block diagram which shows an example of a structure of the X-ray diagnostic apparatus contained in the medical image diagnostic system which concerns on one Embodiment. It is a block diagram which shows an example of a structure of the ultrasonic diagnosing device contained in the medical image diagnostic system in the embodiment. It is a sequence diagram for demonstrating the operation | movement in the embodiment. It is a timing chart which shows an example of the method of determining the timing of the trigger which shows the acquisition start of the X-ray image in the embodiment. It is a timing chart which shows an example of the method of determining the timing of the trigger which shows the acquisition start of the X-ray image in the embodiment. 12 is a timing chart showing an example of a method for calculating a cardiac cycle when an arrhythmia occurs in the first modification of the embodiment. 12 is a timing chart showing an example of a method for calculating a cardiac cycle when an arrhythmia occurs in the second modification of the embodiment.

  Hereinafter, an embodiment will be described with reference to the drawings. Elements that are the same as or similar to those already described are denoted by the same or similar reference numerals, redundant description is omitted, and elements that have not been described are mainly described.

  FIG. 1 is a block diagram illustrating a configuration example of an X-ray diagnostic apparatus 1 included in a medical image diagnostic system according to an embodiment. The X-ray diagnostic apparatus 1 includes a bed having an X-ray high voltage apparatus 2, an X-ray tube 3, an X-ray detector 4, a support frame 5, and a top plate 6, an image generation circuit 7, a communication interface circuit 8, An input interface circuit 9, a control circuit 10, a processing circuit 11, a storage circuit 12, and a display circuit 13 are provided.

  The X-ray high voltage apparatus 2 generates a tube current supplied to the X-ray tube 3 and a tube voltage applied to the X-ray tube 3. The X-ray high voltage apparatus 2 supplies tube currents suitable for X-ray imaging and X-ray fluoroscopy to the X-ray tube 3 under the control of the control circuit 10 and is suitable for X-ray imaging and X-ray fluoroscopy, respectively. The tube voltage is applied to the X-ray tube 3.

  The X-ray tube 3 generates X-rays based on the tube current supplied from the X-ray high voltage device 2 and the tube voltage applied by the X-ray high voltage device 2. X-rays generated from the X-ray tube 3 are applied to the subject P. The X-ray tube 3 may be, for example, a rotary anode type X-ray tube or another type of X-ray tube such as a fixed anode type X-ray tube.

  The X-ray detector 4 detects X-rays generated from the X-ray tube 3 and transmitted through the subject P. The X-ray detector 4 includes, for example, a flat panel detector (FPD). The FPD has a plurality of semiconductor detection elements. The semiconductor detection element includes a direct conversion type and an indirect conversion type. The direct conversion type is a type in which incident X-rays are directly converted into electrical signals. The indirect conversion form is a form in which incident X-rays are converted into light by a phosphor and the light is converted into an electrical signal. An image intensifier may be used as the X-ray detector 4.

  Electrical signals generated by a plurality of semiconductor detection elements as X-rays are incident are output to an analog-to-digital converter (A / D converter) (not shown). The A / D converter converts an electrical signal into digital data. The A / D converter outputs digital data to the image generation circuit 7.

  The support frame 5 movably supports the X-ray tube 3 and the X-ray detector 4 that are arranged to face each other. Specifically, the support frame 5 corresponds to a C arm. As the support frame 5, an Ω arm may be used instead of the C arm. Further, the support frame 5 is not limited to a structure with a C arm and an Ω arm, and has, for example, a structure with two arms (for example, a robot arm) that independently support the X-ray tube 3 and the X-ray detector 4. You may do it. The support frame 5 is not limited to the over tube system, the under tube system, and the like, and can be applied to any form.

  A couch (not shown) has a top 6 (also referred to as a prone table) on which the subject P is placed. A subject P is placed on the top 6.

  For example, the driving device (not shown) drives the support frame 5 and the bed under the control of the control circuit 10. At the time of X-ray fluoroscopy and X-ray imaging, the subject P placed on the top 6 is placed between the X-ray tube 3 and the X-ray detector 4. The driving device may rotate the X-ray detector 4 with respect to the X-ray tube 3 under the control of the control circuit 10.

  The image generation circuit 7 generates an X-ray image based on digital data output from the X-ray detector 4 via an A / D converter (not shown). For example, the image generation circuit 7 generates a plurality of X-ray images taken in time series. The image generation circuit 7 outputs the generated X-ray image to the storage circuit 12 or the like. The image generation circuit 7 associates the generated X-ray image with the electrocardiogram waveform and time information of the subject P acquired from an electrocardiograph (not shown), and outputs them to the storage circuit 12 or the like. May be. Further, the image generation circuit 7 may output the generated X-ray image to the display circuit 13.

  The communication interface circuit 8 is a circuit relating to, for example, a network, the ultrasonic diagnostic apparatus 20, and an external storage device (not shown). Data of the X-ray image obtained by the X-ray diagnostic apparatus 1 can be transferred to another apparatus via the communication interface circuit 8 and the network. Further, the communication interface circuit 8 can receive an ultrasonic image or the like from the ultrasonic diagnostic apparatus 20. Hereinafter, when information is exchanged via the communication interface circuit 8, the description “through the communication interface circuit 8” is omitted.

  The input interface circuit 9 includes an X-ray imaging condition desired by the operator, an X-ray irradiation condition such as an X-ray fluoroscopic condition, a fluoroscopic / imaging position, an irradiation range, and a region of interest in the X-ray image (region of interest). : ROI) or the like is input according to the operator's instruction. Specifically, the input interface circuit 9 captures various instructions, commands, information, selections, and settings from the operator into the X-ray diagnostic apparatus 1.

  The input interface circuit 9 includes a joystick for setting a region of interest, a trackball, a switch button, a mouse, a keyboard, a touch pad for performing an input operation by touching an operation surface, and a display screen and a touch pad. This is realized by a touch panel display or the like. The input interface circuit 9 is connected to the control circuit 10 and converts the input operation received from the operator into an electrical signal and outputs it to the control circuit 10.

  In the present specification, the input interface circuit 9 is not limited to one having physical operation components such as a mouse and a keyboard. For example, an example of the input interface circuit 9 includes an electric signal processing circuit that receives an electric signal corresponding to an input operation from an external input device provided separately from the apparatus and outputs the received electric signal to the control circuit 10. included.

  The control circuit 10 includes, for example, a processor and a memory as hardware resources. The control circuit 10 is, for example, a processor that controls each circuit and driving device in the X-ray diagnostic apparatus 1. The control circuit 10 temporarily stores information such as an operator instruction input from the input interface circuit 9 and information on a start trigger (described later) indicating the start of acquisition of the X-ray image acquired by the processing circuit 11 in a memory. Remember me. The control circuit 10 controls the X-ray high-voltage device 2 and the drive device in order to perform X-ray imaging and X-ray fluoroscopy in accordance with an operator instruction stored in the memory and a start trigger related to the start of X-ray image acquisition. Control. Further, the control circuit 10 controls the X-ray image generation processing in the image generation circuit 7 and the superimposed image generation processing in the processing circuit 11 in accordance with an operator instruction stored in the memory.

  The processing circuit 11 includes, for example, a processor and a memory as hardware resources. The processing circuit 11 reads the control program stored in the storage circuit 12 in response to a start instruction input by the operator via the input interface circuit 9. The processing circuit 11 executes each function for generating a superimposed image in which an X-ray image and a medical image (for example, an ultrasound image) are superimposed according to the read control program. The above functions include, for example, a start trigger acquisition function 11a, a frame rate setting function 11b, a first acquisition function 11c, a second acquisition function 11d, and a superimposed image generation function 11e. Note that the processing circuit 11 may create a moving image by processing a plurality of X-ray images along the time series stored in the storage circuit 12.

  The start trigger acquisition function 11a is a function for acquiring a start trigger indicating the start of X-ray image acquisition from the ultrasound diagnostic apparatus 20. At this time, the control circuit 10 performs control related to the start of X-ray image acquisition triggered by the start trigger.

  The frame rate setting function 11b acquires a frame rate (first frame rate) related to acquisition of an ultrasound image from the ultrasound diagnostic apparatus 20, and based on the first frame rate related to acquisition of an ultrasound image, an X-ray image A second frame rate related to acquisition is set.

  The first acquisition function 11c is a function for acquiring an X-ray image of the subject P from the storage circuit 12 in real time. Specifically, the first acquisition function 11c acquires an X-ray image of the subject in real time at the second frame rate, triggered by the start trigger. Here, “real time” means “every short period”, specifically “every short period determined by the second frame rate”. The first acquisition function 11c outputs the acquired X-ray image to the superimposed image generation function 11e. The X-ray image may be associated with the biological information of the subject P. The biological information corresponds to, for example, an electrocardiogram waveform or a respiratory waveform of the subject P. The respiratory waveform is acquired by, for example, a respiratory sensor (not shown).

  The second acquisition function 11d is a function for acquiring, in real time, an ultrasonic image that is a medical image of the subject P from the ultrasonic diagnostic apparatus 20 that is another modality. Specifically, the second acquisition function 11d acquires in real time an ultrasound image whose time series matches the X-ray image in parallel with the acquisition of the X-ray image by the first acquisition function 11c. Here, “real time” means “every short period”, and specifically means “every short period determined by the first frame rate”. The second acquisition function 11d outputs the acquired ultrasonic image to the superimposed image generation function 11e. Note that the ultrasonic image may be associated with biological information of the subject P. An “ultrasonic image whose time series coincides with an X-ray image” may be called “an ultrasonic image synchronized with an X-ray image” or “an ultrasonic image corresponding to a dynamic change of an X-ray image”. Good.

  The superimposed image generation function 11e is a function that sequentially generates superimposed images by superimposing the X-ray image output from the first acquisition function 11c and the ultrasonic image output from the second acquisition function 11d. . The X-ray image and the ultrasonic image received by the superimposed image generation function 11e have the same acquisition start time according to the X-ray irradiation start trigger received from the ultrasonic diagnostic apparatus 20. Therefore, the superimposed image generation function 11e can generate a superimposed image without time lag in the superimposition of the X-ray image and the ultrasonic image.

  The X-ray image and ultrasonic image to be superimposed may be either a two-dimensional image or a three-dimensional image acquired in real time. A three-dimensional image acquired in real time may be referred to as a four-dimensional image. The form of the superimposed image may be a form in which the images of the target organs are superimposed, or a form in which the target organs are arranged. In the former case, for example, there is a form in which a cross-sectional image (ultrasonic image) of the heart is superimposed on the position of the heart on the fluoroscopic image. Further, for example, there is a form in which a cross-sectional image (ultrasound image) of the heart is superimposed on a 3D blood vessel image (X-ray image) of the heart by an angiography method. In the latter case, a desired image may be arranged.

  Note that the superimposed image generation function 11e may perform alignment of both images when the X-ray image and the ultrasonic image are superimposed. As an alignment method, for example, when the ultrasound probe is a transesophageal probe, by detecting the coordinates of the transesophageal probe from the transesophageal probe image in the X-ray image, the coordinate system of the X-ray image and the ultrasonic wave are detected. A technique for associating with the image coordinate system can be used. This technique is not limited to a transesophageal probe, and can be similarly used as long as it is an in-vivo probe that transmits ultrasonic waves from the inside of the subject P. Further, for example, when the ultrasonic probe is an external probe, by detecting the coordinates of the ultrasonic probe based on the output of the position sensor attached to the ultrasonic probe, the coordinate system of the X-ray image and the ultrasonic image A technique for associating with a coordinate system can be used. As another method of alignment, for example, a method is used in which a specific shape portion in the subject is used as a landmark, and the coordinates of the landmark in the X-ray image are associated with the coordinates of the landmark in the ultrasonic image. Is possible.

  The storage circuit 12 includes a memory for recording electrical information such as an HDD (Hard Disk Drive), and peripheral circuits such as a memory controller and a memory interface associated with the memory. The memory is not limited to HDD, but SSD (solid state drive), magnetic disk (floppy (registered trademark) disk, hard disk, etc.), optical disk (CD, DVD, Blu-ray (registered trademark), etc.), semiconductor memory, etc. Can be used as appropriate.

  The storage circuit 12 includes various X-ray images generated by the image generation circuit 7, a superimposed image generated by the processing circuit 11, a system control program of the X-ray diagnostic apparatus 1, a diagnostic protocol executed by the control circuit 10, and an input Various data groups such as an operator's instruction sent from the interface circuit 9, imaging conditions related to X-ray imaging and fluoroscopic conditions related to X-ray fluoroscopy, error information, and the communication interface circuit 8 and the network. Various data are stored.

  The display circuit 13 includes a display that displays a medical image, an internal circuit that supplies a display signal to the display, and peripheral circuits such as a connector and a cable that connect the display and the internal circuit. The display displays an input screen related to input of fluoroscopy / imaging position, X-ray irradiation conditions, and the like.

  The display displays superimposed images generated sequentially by the processing circuit 11. The display may display a plurality of X-ray images generated by the image generation circuit 7 alone or in a moving image in a region different from the superimposed image. The display may display a moving image by arranging the X-ray image, the ultrasonic image, and the superimposed image.

  FIG. 2 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus 20 included in the medical image diagnostic system. The ultrasonic diagnostic apparatus 20 includes an ultrasonic probe 21, an input interface circuit 22, a display circuit 23, an electrocardiograph 24, a transmission / reception circuit 25, a B-mode data generation circuit 26, a Doppler data generation circuit 27, An image generation circuit 28, a communication interface circuit 29, a storage circuit 30, a control circuit 31, and a processing circuit 32 are provided.

  The ultrasonic probe 21 includes a plurality of piezoelectric vibrators, a matching layer provided on the ultrasonic radiation surface side of the piezoelectric vibrator, a backing material provided on the back side of the piezoelectric vibrator, and the like. Each of the plurality of piezoelectric vibrators generates an ultrasonic wave in response to a drive signal supplied from the transmission / reception circuit 25. The ultrasonic probe 21 is, for example, a transesophageal echocardiography (TEE) probe.

  The input interface circuit 22 captures various instructions, commands, information, selections, and settings from the operator into the ultrasonic diagnostic apparatus 20. The input interface circuit 22 is realized by a trackball, a switch button, a mouse, a keyboard, a touch pad that performs an input operation by touching an operation surface, and a touch panel display in which a display screen and a touch pad are integrated. The input interface circuit 22 is connected to the control circuit 31, converts the input operation received from the operator into an electrical signal, and outputs the electrical signal to the control circuit 31.

  In the present specification, the input interface circuit 22 is not limited to one having physical operation components such as a mouse and a keyboard. For example, an example of the input interface circuit 22 includes an electric signal processing circuit that receives an electric signal corresponding to an input operation from an external input device provided separately from the apparatus and outputs the received electric signal to the control circuit 31. included.

  The display circuit 23 includes a display that displays an ultrasonic image, an internal circuit that supplies a display signal to the display, and peripheral circuits such as a connector and a cable that connect the display and the internal circuit. The display displays an input screen for the operator to input various setting requests. The display displays various images generated by the image generation circuit 28.

  The electrocardiograph 24 acquires an electrocardiogram (ECG) of the subject P via an electrode (not shown) attached to the subject P. The electrocardiograph 24 outputs the acquired electrocardiographic waveform together with time information to the processing circuit 32 via the communication interface circuit 29. The electrocardiograph 24 may output the acquired electrocardiographic waveform together with time information to the image generation circuit 28 via the communication interface circuit 29. The electrocardiograph 24 may output the acquired electrocardiogram waveform together with time information to the image generation circuit 7 of the X-ray diagnostic apparatus 1. The electrocardiograph 24 may be an external device that is not built in the ultrasound diagnostic apparatus 20 or may be built in the X-ray diagnostic apparatus 1.

  The transmission / reception circuit 25 includes a pulse generator, a transmission delay circuit, and a pulser circuit, and supplies a drive signal to each of the plurality of piezoelectric vibrators in the ultrasonic probe 21. The pulse generator repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency frHz (cycle: 1 / fr second). The transmission delay circuit provides each rate pulse with a delay time necessary for converging the transmission ultrasonic wave into a beam and determining transmission directivity. The pulsar circuit applies a voltage pulse as a drive signal to each piezoelectric vibrator of the ultrasonic probe 21 at a timing based on the rate pulse. Thereby, the ultrasonic beam is transmitted to the subject P.

  The transmission / reception circuit 25 further includes a preamplifier, an analog-to-digital converter (A / D converter), a reception delay circuit, and an adder. Based on the reception echo signal generated by each piezoelectric vibrator, Generate a received signal. The preamplifier amplifies the echo signal from the subject P captured via the ultrasonic probe 21 for each channel. The A / D converter converts the amplified received echo signal into a digital signal. The reception delay circuit gives a delay time necessary for determining the reception directivity to the reception echo signal converted into the digital signal. The adder adds a plurality of echo signals given delay times. By this addition, the transmission / reception circuit 25 generates a reception signal in which the reflection component from the direction corresponding to the reception directivity is emphasized. The overall directivity of ultrasonic transmission / reception is determined by the transmission directivity and the reception directivity. This total directivity determines the ultrasonic beam (so-called “ultrasonic scanning line”).

  The B mode data generation circuit 26 includes an envelope detector and a logarithmic converter, and generates B mode data based on the received signal. The envelope detector performs envelope detection on the received signal. The logarithmic converter performs logarithmic conversion on the envelope-detected signal, and relatively emphasizes weak signals in the envelope-detected signal. The B mode data generation circuit 26 generates a signal value (referred to as B mode data) for each depth in each scanning line based on the signal emphasized by the logarithmic converter. The B-mode data generation circuit 26 generates volume data corresponding to the three-dimensional B-mode data based on the two-dimensional B-mode data by the two-dimensional scan or the reception signal by the three-dimensional scan.

  The Doppler data generation circuit 27 includes a mixer, a low pass filter (LPF), and the like, and generates Doppler data based on the received signal. The mixer multiplies the received signal by a reference signal having the frequency f0 of the transmission ultrasonic wave, and generates a signal having a Doppler shift frequency fd component and a signal having a frequency component of (2f0 + fd). The LPF removes a high frequency component (2f0 + fd) signal from the signal output from the mixer. Thereby, the Doppler data generation circuit 27 generates Doppler data having a component of the Doppler shift frequency fd in the received signal.

  The image generation circuit 28 includes a digital scan converter (DSC), an image memory, etc., all not shown. The DSC converts a scanning line signal sequence of ultrasonic scanning composed of B-mode data and Doppler data into a scanning line signal sequence of a video format (scan conversion). The image generation circuit 28 synthesizes character information of various parameters, memory, and the like with the scan-converted B-mode data and Doppler data, and generates image data (also referred to as an ultrasonic image). The image data is data for display, while the B-mode data, volume data, and Doppler data are also called raw data (Raw Data). The image memory stores a plurality of image data corresponding to a series of frames immediately before the input of the freeze operation. The plurality of image data stored in the image memory is used for moving image display (cine display) of an ultrasonic image. The image generation circuit 28 outputs the generated ultrasonic image to the storage circuit 30 or the like. The image generation circuit 28 may associate the generated ultrasonic image with the electrocardiogram waveform and time information of the subject P and output them to the storage circuit 12 or the like.

  The communication interface circuit 29 is, for example, a circuit related to the network, the X-ray diagnostic apparatus 1, and an external storage device (not shown). The data of the ultrasonic image obtained by the ultrasonic diagnostic apparatus 20 can be transferred to another apparatus via the communication interface circuit 29 and the network. Further, the communication interface circuit 29 can transmit an ultrasonic image or the like to the X-ray diagnostic apparatus 1. Hereinafter, when information is exchanged via the communication interface circuit 29, the description “through the communication interface circuit 29” is omitted.

  The storage circuit 30 includes a memory for recording electrical information such as an HDD (Hard Disk Drive), and peripheral circuits such as a memory controller and a memory interface associated with the memory. As the memory, not only HDD but SSD (solid state drive), magnetic disk (floppy disk, hard disk, etc.), optical disk (CD, DVD, Blu-ray, etc.), semiconductor memory, etc. can be used as appropriate. Yes.

  The storage circuit 30 corresponds to various ultrasonic images generated by the image generation circuit 28, a system control program of the ultrasonic diagnostic apparatus 20, a program related to ultrasonic transmission / reception, various processes executed by the control circuit 31 and the processing circuit 32. Program, an operator instruction sent from the input interface circuit 22, and various data sent via the communication interface circuit 29 and the network.

  The control circuit 31 includes, for example, a processor and a memory as hardware resources. The control circuit 31 is, for example, a processor that controls each circuit in the ultrasonic diagnostic apparatus 20. The control circuit 31 temporarily stores information such as an operator instruction input from the input interface circuit 22 in a memory. The control circuit 31 controls the ultrasonic image generation processing in the image generation circuit 28, the start trigger generation processing in the processing circuit 32, and the like according to an operator instruction stored in the memory.

  The processing circuit 32 includes, for example, a processor and a memory as hardware resources. The processing circuit 32 reads the control program stored in the storage circuit 30 in response to the start instruction input via the input interface circuit 22 by the operator. The processing circuit 32 executes each function for generating a start trigger indicating the start of X-ray image acquisition in the X-ray diagnostic apparatus 1 according to the read control program. The above functions include, for example, a waveform detection function 32a, a cardiac cycle calculation function 32b, an acquisition cycle calculation function 32c, and a start trigger generation function 32d. Note that the processing circuit 32 may create a moving image by processing an ultrasonic image along the time series stored in the storage circuit 30.

  The waveform detection function 32 a detects the electrocardiographic waveform of the subject received from the electrocardiograph 24. Specifically, the waveform detection function 32a detects, for example, the peak of the R wave from the electrocardiographic waveform of the subject.

  The cardiac cycle calculation function 32b calculates a cardiac cycle from the detected electrocardiogram waveform. Specifically, the cardiac cycle calculation function 32b calculates a cardiac cycle from, for example, an R wave peak interval in an electrocardiographic waveform.

  The acquisition cycle calculation function 32c calculates the acquisition start interval of the ultrasonic image using the calculated cardiac cycle and the frame rate related to acquisition of the ultrasonic image. As a frame rate for acquiring an ultrasonic image, for example, a value of about 120 [fps] is used in the case of a two-dimensional image, and a value of about 2 [fps] is used in the case of a three-dimensional image. A value is used.

  The start trigger generation function 32d generates a start trigger indicating the start of X-ray image acquisition by the X-ray diagnostic apparatus 1 based on the acquisition start interval.

  Next, the operation of the diagnostic imaging system configured as described above will be described using the sequence diagram of FIG. 3 and the timing chart of FIG. The following description mainly describes a start trigger generation process by the processing circuit 32 of the ultrasonic diagnostic apparatus 20 and a superimposed image generation process by the processing circuit 11 of the X-ray diagnostic apparatus 1. These processes are started by the operation of the operator.

  First, the subject P is placed on the couch top 6 and the electrodes of the electrocardiograph 24 are attached to the subject P. Thereby, the electrocardiograph 24 acquires the electrocardiogram waveform of the subject P, and outputs this electrocardiogram waveform to the processing circuit 32 and the X-ray diagnostic apparatus 1 together with the time information.

  Next, the transesophageal probe which is the ultrasonic probe 21 is inserted into the esophagus of the subject P, and the distal end portion of the transesophageal probe is positioned below the heart of the subject P. As a result, the ultrasonic diagnostic apparatus 20 generates an ultrasonic image based on the output of the transesophageal probe, and attaches an electrocardiographic waveform and time information to the ultrasonic image.

  The X-ray diagnostic apparatus 1 sets an imaging condition of the subject P by an operator's operation and then waits for the start of X-ray fluoroscopy or X-ray imaging of the subject P. Thereafter, step S11 is started.

  In step S <b> 11, the waveform detection function 32 a detects the electrocardiographic waveform of the subject received from the electrocardiograph 24. Specifically, the waveform detection function 32a detects the position (FIG. 4B) indicating the peak of the R wave from the electrocardiographic waveform (FIG. 4A) of the subject. The peak of the electrocardiographic waveform to be detected is not limited to the R wave, but a Q wave, an S wave, or the like may be used.

In step S12, the cardiac cycle calculation function 32b calculates a cardiac cycle from the detected electrocardiogram waveform. Specifically, the cardiac cycle calculation function 32b calculates the cardiac cycle T _C from the interval between the R wave peaks in the electrocardiographic waveform. In FIG. 4, it is assumed that the time between time t ₀ and time t ₁ is 1 second. That is, since the cardiac cycle T _C is 1 second, the heart rate of the subject P is 60.

In step S13, the acquisition cycle calculation function 32c determines the calculated cardiac cycle and a frame rate related to acquisition of an ultrasound image (which may be referred to as “medical image” or “first medical image”) , Which may be referred to as “first frame rate” or “frame rate X”), the ultrasonic image acquisition start interval is calculated. Specifically, acquisition period calculation function 32c, relative to the cardiac cycle T _C, the frame rate to obtain an ultrasound image X to fit update timing (FIG. 4 (d)), the acquisition start interval T _D calculate. The frame rate X indicates that X (X [fps]) ultrasonic images are acquired, generated, or displayed per second. In FIG. 4, since the cardiac cycle T _C is 1 second, which is the same as the frame rate update timing, the acquisition start interval T _D is also 1 second.

On the other hand, FIG. 5 shows an example in which the cardiac cycle does not coincide with the frame rate update timing. In the example shown in FIG. 5A and FIG. 5B, since the cardiac cycle T _C is 0.8 seconds and the frame rate update timing T is 1 second, the cardiac cycle T _C and the update timing T The time length of one cycle does not match. Therefore, and FIG. 5 (c) and as shown in FIG. 5 (d), by a 4-second is a period cardiac cycle T _C and the update timing T coincides with acquisition start interval T _D, the acquisition of X-ray images Start can be set easily.

In step S14, the start trigger generation function 32d generates a start trigger indicating the start of X-ray image acquisition by the X-ray diagnostic apparatus 1 based on the acquisition start interval. Specifically, start trigger generating function 32d from the time of starting the acquisition of ultrasound images (FIG. 4 (c)) (time t _1), shows the acquisition start of X-ray images in a period of acquisition start interval T _D A trigger (FIG. 4 (e)) is generated. In FIG. 4, the trigger indicating the start of X-ray image acquisition is generated at time t ₂ , but the trigger may be generated at time t _{3 when} 2T _{D has} elapsed from time t ₁ . Note that “X-ray image acquisition start” may be appropriately read as “X-ray image generation start” or “X-ray irradiation start”.

  In step S <b> 15, the ultrasonic diagnostic apparatus 20 uses the X-ray diagnostic apparatus 1 for the trigger (this is also referred to as “X-ray image acquisition start trigger” or “start trigger”) and the frame rate X. To the processing circuit 11. Note that the ultrasonic diagnostic apparatus 20 may output the frame rate X to the X-ray diagnostic apparatus 1 in advance before step S15. Further, the ultrasonic diagnostic apparatus 20 may present a plurality of frame rates to the X-ray diagnostic apparatus 1 including a frame rate obtained by multiplying the frame rate X by an integer. The “integer multiple” may be referred to as “positive integer multiple” or “natural number multiple”.

  In step S <b> 16, the start trigger acquisition function 11 a of the X-ray diagnostic apparatus 1 receives an X-ray image acquisition start trigger from the ultrasound diagnostic apparatus 20. At this time, the control circuit 10 performs control related to acquisition of an X-ray image triggered by an X-ray image acquisition start trigger.

  In step S <b> 17, the frame rate setting function 11 b receives the frame rate X from the ultrasound diagnostic apparatus 20. Based on the frame rate X, the frame rate setting function 11b is a frame rate related to acquisition of an X-ray image (second medical image) (this is also referred to as “second frame rate” or “frame rate Y”). Set. Specifically, the frame rate setting function 11b sets the frame rate Y (FIG. 4F) to an integer multiple of the frame rate X. For example, if the frame rate X is 4 [fps], the frame rate setting function 11b sets the frame rate Y to 4 [fps], 8 [fps], or the like. The frame rate setting function 11b may set the frame rate Y to a divisor of the frame rate X in accordance with the modality performance and the like. The frame rate setting function 11b may set the frame rate by calculation, or may set the frame rate by referring to a table storing a list of frame rates. Moreover, step S17 may be performed before step S16.

  In step S18, the X-ray diagnostic apparatus 1 generates an X-ray image of the subject at the second frame rate triggered by an X-ray image acquisition start trigger.

  In step S19, the first acquisition function 11c acquires an X-ray image of the subject from the X-ray diagnostic apparatus 1 in real time at the second frame rate, triggered by an X-ray image acquisition start trigger.

  In step S20, the ultrasound diagnostic apparatus 20 generates an ultrasound image of the subject at the first frame rate.

  In step S <b> 21, the ultrasonic diagnostic apparatus 20 outputs an ultrasonic image to the processing circuit 11 of the X-ray diagnostic apparatus 1.

  In step S22, the second acquisition function 11d acquires an ultrasonic image of the subject from the ultrasonic diagnostic apparatus 20 in real time in parallel with the acquisition of the X-ray image in step S19. That is, step S19 and step S22 may be performed simultaneously.

  In step S23, the superimposed image generation function 11e sequentially generates superimposed images by superimposing the X-ray image acquired in step S19 and the ultrasonic image acquired in step S22.

  In step S24, the display circuit 13 displays the superimposed images sequentially generated by the processing circuit 11 as a moving image.

  As described above, according to one embodiment, the ultrasonic diagnostic apparatus generates a start trigger indicating the start of X-ray image acquisition in the X-ray diagnostic apparatus. The X-ray diagnostic apparatus generates and acquires an X-ray image using the start trigger as a trigger. The X-ray diagnostic apparatus sets a frame rate related to X-ray image acquisition based on the frame rate related to ultrasonic image acquisition of the ultrasonic diagnostic apparatus. Then, the X-ray diagnostic apparatus sequentially generates a superimposed image in which the acquired X-ray image and the ultrasonic image are superimposed.

  Therefore, when superimposing images acquired in real time from different modalities, it is possible to generate a superimposed image in time series.

  According to one embodiment, the second frame rate related to X-ray image acquisition is set to an integer multiple of the first frame rate related to ultrasonic image acquisition.

  Therefore, it is possible to prevent a visual shift of the superimposed image caused by a mismatch in the frame rate of the image (for example, when one frame rate is not an integral multiple of the other frame rate). A high superimposed image can be provided. Then, by using a highly visible superimposed image, treatment based on accurate information is possible, and improvement in procedure efficiency can be expected.

  Moreover, according to one embodiment, since the biological information is an electrocardiogram waveform, it is possible to generate a start trigger with high accuracy in acquiring an X-ray image for an organ that moves according to a heartbeat.

  According to one embodiment, since the medical image is an ultrasound image, the X-ray image acquired in real time and the ultrasound image can be superimposed to generate a superimposed image in time series. it can. For example, an angiographic X-ray image clearly includes contrast agent and catheter, but does not include a heart valve. Ultrasound images include contrast agents, catheters, and heart valves, but may be unclear and difficult to view. In the first embodiment, by superimposing such an X-ray image and an ultrasonic image, it is possible to generate a superimposed image that includes a contrast agent, a catheter, and a heart valve and is easy to visually recognize.

  In addition, the configuration in which both the X-ray image and the medical image are acquired in real time can generate a superimposed image following a dynamic change, unlike when either one is a previously acquired image. Image-based treatment is possible. For example, when one of the images is acquired in advance, the heartbeat does not match with the image acquired in real time, and a superimposed image following a dynamic change cannot be generated. On the other hand, in this embodiment, since both the X-ray image and the ultrasonic image are acquired in real time, a superimposed image following a dynamic change can be generated.

  In the embodiment, the example in which the start trigger of the X-ray diagnostic apparatus is generated by the processing circuit of the ultrasonic diagnostic apparatus has been described. However, the start trigger of the ultrasonic diagnostic apparatus is generated by the processing circuit of the X-ray diagnostic apparatus. Even if the configuration is modified, the same effect can be obtained. Supplementally, as described in one embodiment, the processing circuit of the ultrasonic diagnostic apparatus is not limited to the case where the frame rate of the X-ray image is set based on the frame rate of the ultrasonic image. Similarly, the present invention is not limited to the case where a value that is an integral multiple of the frame rate is presented from the ultrasonic diagnostic apparatus side to the X-ray diagnostic apparatus side. For example, one embodiment may be modified so that the processing circuit of the X-ray diagnostic apparatus sets the frame rate of the ultrasonic image based on the frame rate of the X-ray image. Similarly, an integer multiple of the frame rate may be presented from the X-ray diagnostic apparatus side to the ultrasonic diagnostic apparatus side. In the embodiment, the example in which the superimposed image is generated by the processing circuit of the X-ray diagnostic apparatus has been described. However, the same effect can be obtained even when the superimposed image is generated by the processing circuit of the ultrasonic diagnostic apparatus. Can be obtained. Even when these modifications are applied to the following modifications, the same effects can be obtained.

(First modification)
Next, a first modification of the embodiment will be described.
In the first modified example, when there is an arrhythmia, the start trigger for X-ray image acquisition is readjusted by regenerating the start trigger at a cycle according to the frequency of the arrhythmia.

  Accordingly, the cardiac cycle calculation function 32b, the acquisition cycle calculation function 32c, and the start trigger generation function 32d in the processing circuit 32 of the ultrasonic diagnostic apparatus 20 have the following functions in addition to the functions described above.

  The cardiac cycle calculation function 32b calculates the cardiac cycle a plurality of times, and when a substantially identical first cardiac cycle and a second cardiac cycle different from the first cardiac cycle are obtained, from the first cardiac cycle And the information on the frequency with which the second cardiac cycle is obtained is output to the acquisition cycle calculation function 32c. Here, as the number of times of calculation of the cardiac cycle, for example, an arbitrary number of 3 or more can be used.

  The acquisition cycle calculation function 32c has a function of recalculating the acquisition start interval based on the frequency information output from the cardiac cycle calculation function 32b.

  The start trigger generation function 32d has a function of regenerating the start trigger based on the recalculated acquisition start interval.

  Other configurations are substantially the same as those of the above-described embodiment.

Next, the operation of the first modified example configured as described above will be described with reference to FIG.
FIG. 6 is a timing chart showing an example of a method for calculating a cardiac cycle when an arrhythmia occurs. Now, after executing step S11 as in the above-described embodiment, in the cardiac cycle calculation process of step S12, each function in the processing circuit 32 of the ultrasonic diagnostic apparatus 20 operates as follows. In FIG. 6, it is assumed that the interval between time t ₀ and time t ₁ is 1 second, and the cardiac cycle T _C is also assumed to be 1 second. Further, it is assumed that the interval between the time t ₄ ′ and the time t ₅ ′ detected after the occurrence of arrhythmia is 1 second. Further, since the cardiac cycle T _C is 1 second, which is the same as the frame rate update timing, the acquisition start interval is also 1 second.

As shown in FIGS. 6A and 6B, the cardiac cycle calculation function 32b calculates the cardiac cycle T _C from the interval between the R wave peaks in the electrocardiographic waveform of the subject (time t _{0 to} t ₂ ). At this time, it is assumed that after time t ₂ , the peak of the R wave is detected at time t _ar and the next peak is detected at time t ₄ ′ (FIG. 6C). That is, the occurrence of arrhythmias, transient short cardiac cycle than the cardiac cycle T _C T _C 'and a long cardiac cycle than the cardiac cycle T _C T _C' 'are calculated. The cardiac cycle calculation function 32b obtains the frequency of arrhythmia from the information of the cardiac cycles T _C ′ and T _C ″ that temporarily fluctuate, and uses the substantially constant cardiac cycle T _C as the cardiac cycle calculation result. The cardiac cycle calculation function 32b outputs the frequency information and the cardiac cycle to the acquisition cycle calculation function 32c.

In other words, the cardiac cycle calculation function 32b is the cardiac cycle to calculate a plurality of times, a first cardiac cycle T _C of the substantially identical to one another, the first cardiac cycle T _C second cardiac cycle T _C which is different from the ', T _C' When 'is obtained, the cardiac cycle composed of the first cardiac cycle T _C and the frequency information for obtaining the second cardiac cycles T _C ′, T _C ″ are output to the acquisition cycle calculation function 32c. The frequency information is, for example, information indicating a cycle in which the second cardiac cycles T _C ′, T _C ″ are obtained.

Thereafter, based on the outputted cardiac cycle, the processes of steps S13 to S24 are executed as described above.
Meanwhile, acquisition period calculation function 32c based on the output information of the frequency, by re-executing the step S13, to re-calculate the acquisition start interval T _D.

Start trigger generating function 32d, based on the acquisition start interval T _D which is recalculated, by re-executing the step S14, to regenerate the start trigger.

  Thereafter, based on the regenerated start trigger, the processes in steps S15 to S24 are performed again as described above. Further, the operation of re-executing steps S13 to S24 is repeatedly executed based on the frequency information.

  As described above, according to the first modification example, when the cardiac cycle is calculated a plurality of times and a first cardiac cycle that is substantially identical to each other and a second cardiac cycle different from the first cardiac cycle are obtained, A cardiac cycle composed of the first cardiac cycle and frequency information for obtaining the second cardiac cycle are output. Thereafter, the acquisition start interval is recalculated based on the frequency information, and the start trigger is regenerated based on the recalculated acquisition start interval. Therefore, even if an arrhythmia occurs in the heartbeat of the subject, the start trigger can be reset at an appropriate timing according to the frequency of the arrhythmia.

(Second modification)
Next, a second modification of the embodiment will be described.
In the second modification, when an arrhythmia is detected, a start trigger is regenerated to readjust the start of X-ray image acquisition. In the second modification, it is assumed that the electrocardiogram waveform is shifted only during a period in which the arrhythmia occurs temporarily, and the acquisition cycle acquired in one embodiment does not change roughly (that is, does not recalculate). )

  Accordingly, the cardiac cycle calculation function 32b and the start trigger generation function 32d in the processing circuit 32 of the ultrasonic diagnostic apparatus 20 have the following functions in addition to the functions described above.

  The cardiac cycle calculation function 32b has a function of outputting the short cardiac cycle to the start trigger generation function 32d when a cardiac cycle shorter than the normal cardiac cycle is detected.

The start trigger generation function 32d has a function of regenerating the start trigger based on a short cardiac cycle.
Other configurations are substantially the same as those of the above-described embodiment.

Next, the operation of the second modified example configured as described above will be described with reference to FIG.
FIG. 7 is a timing chart showing an example of a method for calculating a cardiac cycle when an arrhythmia occurs. After executing step S11 as in the above-described embodiment, in the cardiac cycle calculation process in step S12, each function in the processing circuit 32 of the ultrasonic diagnostic apparatus 20 operates as follows. In FIG. 7, it is assumed that the time between time t ₀ and time t ₁ is 1 second, and the cardiac cycle T _C is also assumed to be 1 second. Further, since the cardiac cycle T _C is 1 second, which is the same as the frame rate update timing, the acquisition start interval is also 1 second.

As shown in FIGS. 7A and 7B, the cardiac cycle calculation function 32b calculates the cardiac cycle T _C from the interval of the R wave peaks in the electrocardiographic waveform of the subject (time t ₀ to time t _2). At this time, it is assumed that after time t ₂ , the peak of the R wave is detected at time t _ar and the next peak is detected at time t ₄ (FIG. 7C). That is, the occurrence of arrhythmias, transient short cardiac cycle than the cardiac cycle T _C T _C 'and a long cardiac cycle than the cardiac cycle T _C T _C' 'are calculated. The cardiac cycle calculation function 32b outputs the temporarily changed cardiac cycle T _C ′ and cardiac cycle T _C ″ to the start trigger generation function 32d.

  In other words, when a cardiac cycle that is different from the normal cardiac cycle is detected, the cardiac cycle calculation function 32b outputs the different cardiac cycle to the start trigger generation function 32d.

Thereafter, based on the outputted cardiac cycle, the processes of steps S13 to S24 are executed as described above. Note that the processing in step S13 is omitted because it has already been performed.
The start trigger generation function 32d regenerates the start trigger by re-executing step S14 based further on the different cardiac cycles that have been output.

  Thereafter, based on the regenerated start trigger, the processes in steps S15 to S24 are performed again as described above. Further, the operation of re-executing steps S12 to S24 is repeatedly performed every time an arrhythmia is detected.

  As described above, according to the second modification, a cardiac cycle different from the original cardiac cycle is detected, and a start trigger indicating the start of X-ray image acquisition is reset based on the different cardiac cycle. Therefore, even if an arrhythmia occurs in the heartbeat of the subject, the start trigger can be reset at an appropriate timing each time the arrhythmia occurs.

  The term “processor” used in the above description is, for example, a CPU, a GPU (Graphics Processing Unit), an application-specific integrated circuit (ASIC), a programmable logic device (for example, a simple programmable logic device (for example, It means circuits such as Simple Programmable Logic Device (SPLD), Complex Programmable Logic Device (CPLD), and Field Programmable Gate Array (FPGA).

  The processor implements various functions by reading and executing a program stored in the storage circuit. Instead of storing the program in the storage circuit, the program may be directly incorporated in the processor circuit. In this case, the processor implements various functions by reading and executing a program incorporated in the circuit.

  Each processor of the present embodiment is not limited to being configured as a single circuit for each processor, but is configured as a single processor by combining a plurality of independent circuits so as to realize various functions thereof. Also good. Furthermore, a plurality of components may be integrated into one processor to realize the function. Each function performed in the processing circuit may be performed in the control circuit.

  The start trigger acquisition function 11a, the frame rate setting function 11b, the first acquisition function 11c, the second acquisition function 11d, the superimposed image generation function 11e, and the display circuit 13 according to the embodiment include the start trigger acquisition in the claims. 3 is an example of a display unit, a frame rate setting unit, a first acquisition unit, a second acquisition unit, a superimposed image generation unit, and a display unit. The cardiac cycle calculation function 32b, the acquisition cycle calculation function 32c, and the start trigger generation function 32d according to an embodiment are examples of the first calculation function, the second calculation function, and the generation function in the claims.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 ... X-ray diagnostic apparatus, 2 ... X-ray high voltage apparatus, 3 ... X-ray tube, 4 ... X-ray detector, 5 ... Support frame, 6 ... Top plate, 7 ... Image generation circuit, 8 ... Communication interface circuit, DESCRIPTION OF SYMBOLS 9 ... Input interface circuit, 10 ... Control circuit, 11 ... Processing circuit, 11a ... Start trigger acquisition function, 11b ... Frame rate setting function, 11c ... First acquisition function, 11d ... Second acquisition function, 11e ... Superimposed image Generation function, 12 ... Memory circuit, 13 ... Display circuit, 20 ... Ultrasound diagnostic device, 21 ... Ultrasonic probe, 22 ... Input interface circuit, 23 ... Display circuit, 24 ... Electrocardiograph, 25 ... Transceiver circuit, 26 ... B mode data generation circuit, 27 ... Doppler data generation circuit, 28 ... Image generation circuit, 29 ... Communication interface circuit, 30 ... Memory circuit, 31 ... Control circuit, 32 ... Processing circuit, 32a ... Waveform detector , 32 b ... cardiac cycle calculating function, 32c acquisition period calculation function, 32d ... start trigger generating function.

Claims (14)

A start trigger acquisition unit for acquiring a start trigger indicating acquisition start of an X-ray image based on the biological information of the subject from other modalities;
A frame rate setting unit that sets a second frame rate related to acquisition of the X-ray image based on a first frame rate related to acquisition of a medical image by the other modality;
Triggered by the start trigger, a first acquisition unit that acquires an X-ray image of the subject in real time at the second frame rate;
In parallel with the acquisition of the X-ray image, a second acquisition unit that acquires the medical image of the subject from the other modality in real time;
A superimposed image generation unit that sequentially generates a superimposed image obtained by superimposing the acquired X-ray image and the acquired medical image;
An X-ray diagnostic apparatus comprising:   The X-ray diagnostic apparatus according to claim 1, wherein the frame rate setting unit sets the second frame rate to an integer multiple of the first frame rate. The X-ray diagnostic apparatus according to claim 1, further comprising a display unit that displays the superimposed image.   The X-ray diagnostic apparatus according to claim 3, wherein the display unit displays the acquired X-ray image in a region different from the superimposed image.   The X-ray diagnosis apparatus according to claim 1, wherein the biological information is an electrocardiogram waveform.   The X-ray diagnostic apparatus according to any one of claims 1 to 5, wherein the medical image is an ultrasound image. A medical diagnostic imaging system including a first modality and a second modality,
The first modality is
A first calculation unit that calculates a period related to biological information of the subject;
A second calculation unit that calculates an acquisition start interval of the first medical image using the cycle and a first frame rate related to acquisition of the first medical image by the first modality;
A generation unit that generates a start trigger indicating the start of acquisition of the second medical image by the second modality based on the acquisition start interval; and
The second modality is
A start trigger acquisition unit for acquiring the start trigger from the first modality;
A frame rate setting unit that sets a second frame rate related to acquisition of the second medical image based on the first frame rate;
Triggered by the start trigger, a first acquisition unit that acquires the second medical image of the subject in real time at the second frame rate;
In parallel with the acquisition of the second medical image, a second acquisition unit that acquires the first medical image of the subject from the first modality in real time;
A medical image diagnostic system comprising: a superimposed image generation unit that sequentially generates a superimposed image in which the acquired second medical image and the acquired first medical image are superimposed.   The medical image diagnostic system according to claim 7, wherein the frame rate setting unit sets the second frame rate to an integer multiple of the first frame rate.   The medical image diagnosis system according to claim 7 or 8, wherein the second modality further includes a display unit that displays the superimposed image.   The medical image diagnosis system according to claim 9, wherein the display unit displays the acquired X-ray image in a region different from the superimposed image. The first medical image is an ultrasound image;
The second medical image is an X-ray image;
The medical image diagnostic system according to any one of claims 7 to 10. When the biological information is an electrocardiogram waveform,
The first calculation unit calculates a cardiac cycle corresponding to the cycle from the electrocardiogram waveform,
The second calculation unit calculates the acquisition start interval using the first frame rate and the cardiac cycle.
The medical image diagnostic system according to any one of claims 7 to 11. The first calculation unit calculates the cardiac cycle a plurality of times, and when the substantially identical first cardiac cycle and a second cardiac cycle different from the first cardiac cycle are obtained, the first cardiac cycle is obtained. Outputting the cardiac cycle consisting of a cycle and information on the frequency with which the second cardiac cycle is obtained to the second calculation unit;
The second calculation unit recalculates the acquisition start interval based on the frequency information,
The generation unit regenerates the start trigger based on the recalculated acquisition start interval.
The medical image diagnostic system according to claim 12. When the first calculation unit detects a cardiac cycle different from the cardiac cycle, the first calculation unit outputs information on the different cardiac cycle to the generation unit,
The generator regenerates the start trigger based further on the different cardiac cycles;
The medical image diagnostic system according to claim 12.